Method and apparatus for combining continuous wave and time domain optical imaging

ABSTRACT

There is provided methods and systems for optical imaging in a turbid medium that combine continuous wave (CW) and time domain (TD) approaches to substantially increase robustness of optical imaging as well as to reduce acquisition times associated with the TD approach. In one aspect, a method is provided that uses CW measurements to scale the values of a temporal point spread function (TPSF) to avoid physical unit mismatch problems. In another aspect, both CW and TD measurements are synergistically combined to estimate optical properties of the medium used in image reconstruction. Optical systems capable of realizing these methods are also provided.

CROSS-REFERENCE TO RELATED APPLICATIONS

[0001] This is the first application filed for the present invention.

TECHNICAL FIELD

[0002] The invention relates to the field of optical imaging of turbid media, such as mammalian tissue. More specifically, the invention relates to optical imaging using both continuous wave and time domain methods.

BACKGROUND OF THE INVENTION

[0003] Imaging of mammalian tissues has been used extensively to obtain information on the internal structures as well as on the biodistribution of molecules. This information can of course be utilized for diagnosis purposes. Several techniques based on different physical principles are currently available to obtain images that encompass a broad range of spatio-temporal resolution. Such techniques include Magnetic Resonance Imaging (MRI), Positron Emission Tomography (PET), single-photon emission computed tomography (SPECT), X-ray, ultrasound and, now emerging, optical imaging.

[0004] In optical imaging three approaches have been used to generate the optical data necessary to reconstruct images of volume of interest (VOI) namely Continuous Wave (CW), which involves the measurement of light attenuation; Time Domain (TD), which involves injecting a pulse of light of short duration within the VOI and detecting the light as a function of time as it exits the VOI; and Frequency Domain (FD), which relies on frequency modulation of the light source and analysis of the phase and amplitude of the signal as it exits the VOI.

[0005] Continuous wave permits rapid acquisition and is the least expensive of the three approaches but provides a limited amount of information. More specifically, in CW imaging, the scatter coefficient of the VOI must be an assumption in order to obtain absorption coefficient information. CW cannot determine absorption separately from scatter. TD provides more information. In TD, a short laser pulse is injected in the part of the mammal to be imaged and the distribution of the time of flight of the photon exiting the volume of interest is measured. The resulting signal is referred to as a temporal point spread function (TPSF) that can be used to calculate such characteristics as the mean time of flight of photons. In FD, the intensity of the source is modulated with high frequency. As a result, a photon density wave propagates in the tissue and the amplitude and phase shift of the wave relative to the incident wave is measured. In principle, by scanning the tissue with a range of different frequencies, the entire TPSF can be reconstructed. However, in practice, a single frequency is usually employed to estimate the mean time of flight of the photons.

[0006] Image reconstruction using optical data belongs to the class of inverse problems. The problem consists of finding the distribution of optical parameters in tissue based on the detected optical signal. While image reconstruction techniques are still the subject of intense research activities, several tested approaches have been used with relative success. Some of these approaches are summarized and described in Boas et al. (IEEE SiG. Proc. Mag., Vol.18, No.6, pp.57-75, 2001) and Hawrysz and Sevick-Muraca (Neoplasia, Vol.2, No.5, pp388-417, 2000).

[0007] TD measurements provide detailed information about the absorption and the scatter from within a tissue, however, the method suffers from long acquisition time, expensive hardware and complicated software analysis. Furthermore the acquisition often results in noisy TPSF data from which accurate estimates of spatial optical information are difficult to obtain.

[0008] It would therefore be desirable to provide a method that would overcome the limitations of CW and TD, while retaining their advantages.

SUMMARY OF THE INVENTION

[0009] The inventor has provided a method and apparatus by which the advantages of TD optical imaging can be exploited while avoiding certain disadvantages. In particular long acquisition times can be substantially reduced.

[0010] In one aspect of the invention there is provided a method for optical imaging of a volume of interest (VOI) in a turbid medium, the method comprising:

[0011] optically scanning the VOI at a plurality of source/detector geometries using continuous wave (CW) to generate a measured attenuation value at one or more wavelength, the measured attenuation value being measured from a continuous light intensity value provided to the source and detected at the detector;

[0012] optically scanning the VOI using time-domain (TD) to generate data representing at least a portion of a measured temporal point spread function (TPSF) at the one or more wavelength, the TPSF data being measured for each of the plurality of source/detector geometries from a plurality of light pulses from which a statistical average of light received as a function of time is obtained, the TPSF data yielding information about absorption and scatter within the VOI; and

[0013] combining information provided by CW and TD, whereby to generate an improved image of the VOI with fewer light pulses and a shorter acquisition time by using both time-domain and continuous wave modalities.

[0014] In another aspect of the invention there is also provided an optical imaging apparatus for imaging a turbid media object, the apparatus comprising: at least one optical source for providing continuous and pulsed optical energy; at least one optical detector for detecting optical energy and generating time-dependent and continuous data; a source/object optical coupling for coupling the optical source to a desired position on the object; a detector/object optical coupling for coupling the optical detector to a desired position on the object; an acquisition controller connected to the optical source and the optical detector for collecting the time-dependent and continuous data for a plurality of source/detector geometries within a volume of interest in the object; a raw TPSF data compiler for receiving a time-dependent output signal from the detector and generating raw TPSF data output; a TPSF data enhancer for processing the raw TPSF data output and the continuous data to provide enhanced TPSF data, wherein the continuous data corresponds to the raw TPSF data output according to the source/detector geometries.

[0015] It will be appreciated that the present invention allows for a number of different possible economies to be achieved by combining CW with TD techniques. Firstly, the estimate of absorption coefficients for a VOI from CW (making an assumption about scatter, such as assuming that scatter is constant for example) can be used as initial values in processing the TD data to yield more accurate absorption coefficients (along with scatter coefficients). Secondly, the process of determining the optical properties of the VOI can involve simultaneously comparing CW model data with CW measured data and comparing TD model data with TD measured data. Thirdly, processing time and acquisition time can be reduced by using an image generated from CW data alone as a less-accurate image, whose purpose is to help in defining a subset of source/detector configurations or geometries to be used in collecting TD data for specific portions of the VOI requiring better detail.

BRIEF DESCRIPTION OF THE DRAWINGS

[0016] Further features and advantages of the present invention will become apparent from the following detailed description, taken in combination with the appended drawings, in which:

[0017]FIG. 1 is a high-level flow chart illustrating the general method according to some embodiments of the present invention;

[0018]FIG. 2 is a block diagram of an imaging apparatus according to another embodiment of the invention in which CW data is used to help in determining optical properties of an VOI of an object being imaged using TPSF data and a TD photon migration model;

[0019]FIG. 3a is a plot of amplitude vs time (bin number) for a TPSF and its first derivative; and

[0020]FIG. 3b is a plot of amplitude vs time (bin number) for the first derivative of a TPSF and its second derivative.

[0021] It will be noted that throughout the appended drawings, like features are identified by like reference numerals.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

[0022] In the present description, by CW measurements it is meant optical signals measured while the light source that illuminates the object to be imaged is continuously on, namely a steady state flux measurement.

[0023] By Time Domain (TD) measurements, it is meant that the optical signal is measured as a function of time following a brief pulse of the light source. The resulting signal is the so-called temporal point spread function (TPSF), and the TPSF data collected may be either one, two, a few or several points on the TPSF (often referred to as different time gates), a single parameter resulting from a plurality of points, such as a slope or other characteristic of the TPSF curve, or the whole TPSF data. When the TD optical detector is a single-photon counting detector, the whole TPSF can be efficiently collected as a result of the measurement technique. When a gated ICCD is used, it is more practical to select time gates. Due to the nature of the detection system, the TPSF data requires a large number of acquisitions (and in comparison to CW, much more time) to achieve relatively stable measured values. In many cases, the TPSF data will be inherently noisy.

[0024] Optical image reconstruction can be based on complex photon propagation models such as Boltzmann transport equation (Arridge, Inv. Prob., Vol. 15, pp.R41-R93, 1999) or on simpler model photon diffusion (migration) equations which incorporate an optical diffusion coefficient, D, which is a function of absorption coefficient μ_(a) and the modified scatter coefficient μ_(s)′. Based on these equation and optical signal measurements, μ_(a) and μ_(s)′ can be estimated and therefore provide a spatial distribution of these optical properties within the object (Hawrysz and Sevick-Muraca, Neoplasia, Vol.2, No.5, pp388-417, 2000).

[0025] Photon diffusion equation can be solved using both CW and TD measurements to predict the photon fluence based on known spatial distribution of μ_(a) and μ_(s)′ with the difference that there is no time dependence for the CW case. However, if these properties are not known a priori they must be calculated or estimated. TD measurements with appropriate processing of the data can yield μ's information, but as mentioned previously requires longer acquisition times. CW measurements are faster and more economical but cannot distinguish between μ_(a) and μ_(s)′.

[0026] In one aspect of the invention, there is provided a method that advantageously combines CW and TD measurements without some of their disadvantages to produce optical images. Thus and referring to FIG. 1, CW and TD data are acquired at 10 and 12 over a given part of an object such as a mammal comprising a volume of interest (VOI) to obtain an attenuation value and a TPSF, and are combined at 14 to produce an image of the VOI. The combination of the data from the two measurement modes permits a more accurate image reconstruction and can also result in substantially reduced acquisition times.

[0027] In one embodiment of the invention the optical properties μ_(a) and μ_(s)′ are estimated using both CW and TD measurements obtained independently, namely without necessarily having the same source/detector geometries. The resulting values of μ_(a) and μ_(s)′ obtained with each modality are compared and are reciprocally adjusted until the difference is less than a predetermined value. In other words, the values of μ_(a) and μ_(s)′ are iteratively adjusted for one modality by taking into account the values obtained with the other modality. This approach advantageously reduces the acquisition times for TD measurements by providing additional information with CW allowing acquisition of TPSF with lower S/N ratios. Alternatively CW and TD data can also be combined to estimate μ_(a) and μ_(s)′ as opposed estimating μ_(a) and μ_(s)′ with each modality.

[0028] It will be appreciated that iteration may be saved if the estimate of μ_(a) by way of CW imaging is used as a starting point for determining μ_(a) and μ_(s)′ by way of TD imaging. Furthermore, the process of imaging and calculating the values for μ_(a) (i.e. by making an assumption about μ_(s)′, for example by holding μ_(s)′ constant) by CW can be carried out in parallel with the acquisition of TPSF data. Preferably, the CW imaging will be completed before the TD data acquisition is completed and determination of μ_(a), μ_(s)′ values begin using the TPSF data. In this way, the μ_(a) data determined by CW can be used as an initial best guess in the TD imaging. Of course, the collection of CW data for the various source/detector geometries as is needed by the CW data processing unit may require little time in comparison with the CW data processing time. Provided that TD data acquisition can continue in parallel with the processing of the CW data, parallel imaging can be provided.

[0029] The above embodiments of the method of the invention can be carried out using a system as described in FIG. 2 in which a combination of CW and TD modalities is described that synergistically integrates the two approaches to provide faster and more accurate estimates of the optical properties of an object. In this regard, a continuous 40 and a pulsed 42 laser source are provided to inject light within an object 41. Also provided are one or more detectors suitable for CW 44 and TD 46 detection. The optical coupling of the sources and detectors at 48 and 50 respectively with the object to provide desired source/detector configurations can be realized using known technologies such as optical fibers, free-space optics and the like.

[0030] The controller 56 has a control output signal to coupling device 48 for selecting the source position. This is preferably achieved by way of an optical switch in the case of a fiber optic coupling, and in the case of free-space optics by way of a galvo-mirror inserted within the optical system. The detector coupling device 50 preferably requires no switching control. This is achieved in the case that the detector has a channel for each detector position, as is practical in the case of a gated ICCD. However, when using free-space optics, the detector position is controlled by galvo-mirror or other means to achieve movement of the detection spot over the object.

[0031] The time resolved detector 46 is linked to a raw TPSF data compiler 52 that can generate TPSF's. Compiler 52 may also comprise a normalizer unit wherein TPSF data can be normalized by the CW data (attenuation) to produce dimensionless data to avoid, for example, experiment-to-theory unit mismatch thereby enabling quick processing of the data. An estimator 54 is provided to estimate values for μ_(a) and μ_(s)′ from the measured optical data and the calculated optical data for the given source/detector geometry. The calculated CW optical data is provided by a calculator 62, while the calculated TD optical data is provided by a calculator 64. In the embodiment of FIG. 2, the TPSF data acquired and enhanced may be the full TPSF, a TPSF characteristic parameter, or a plurality of time-gate TPSF points.

[0032] The modes (CW or TD) and the sequences of data acquisition are controlled by an acquisition controller 56. In particular the acquisition controller can advantageously dynamically control the acquisition of data based on the information received by the detectors. Once the acquisition is completed the image data is stored in raw image data store 58.

[0033] It will be appreciated that the system can be modified and still achieve similar results. For example, a single laser source that can provide a continuous as well as pulsed output can be used. Also a single detector can be used to detect continuous or time resolved signals. Other modifications as would be obvious to one skilled in the art are also considered to be within the scope of the invention.

[0034] The apparatus of FIG. 2 can be used in a variety of ways. Firstly, the estimator 54 can process CW data for a VOI. This is done by making an assumption about μ_(s)′ value for the whole VOI. While this assumption may be wrong, it allows for an estimation of μ_(a) that is close in some cases, and at least a useful first approximation in other cases. The resulting 3D map of μ_(a) and μ_(s)′ stored in store 58 would have the assumed μ_(s)′ values (which could be constant values), and a first approximation of β_(a). In estimating both μ_(a) and μ_(s)′ using the TD optical data, the assumed μ_(s)′ value and the first approximation of the μ_(a) values is fed to calculator 64. The estimator 54 will compare the resulting calculated TPSF optical data to the measured TPSF data to determine in a first pass an adjustment to both μ_(a) and μ_(s)′. This may be done for more than one TPSF time gate in the case that time gate values are used. The mode of operation allows for the possibility of acquiring CW data and processing it to obtain the first approximation of μ_(a) for the whole VOI or object, while acquisition of raw data on the TD side continues during CW calculation time (but not during CW data acquisition unless parallel optical data acquisition hardware is provided).

[0035] Secondly, the estimator 54 can compare the CW and TD calculated and measured optical data together and decide on a best value for μ_(a) and μ_(s)′. In this case, the calculator 62 uses the μ_(a) and μ_(s)′ data in which there is no assumption about μ_(s)′ values. Since the CW data is less noisy, a better estimate of μ_(a) and μ_(s)′ is obtained using both the CW and TD data than with the TD data alone. While this second approach may be done wholly simultaneously, namely CW and TD acquisition and data processing together, it may also be done following a first CW pass as in the first approach.

[0036] Thirdly, it will be appreciated that the apparatus of FIG. 2 can be used to obtain a CW image prior to imaging by TD. In this case, the CW image may be used to select a specific portion of the object 41 that would require better resolution by TD imaging. In this case, an input to the acquisition controller 56 (not shown) is provided to select the specific VOI to be imaged by TD. The CW-based image data in store 58 would then be enhanced by the TD data. Again, for the specific VOI, the CW data could be re-measured or retrieved from a data store (not shown) and used in conjunction with the TD data to enhance image reconstruction. By reducing the volume to image by TD, image acquisition and reconstruction data processing time is saved.

[0037] For example CW can be used to find a lesion (VOI) within a breast, while TD measurements can be used to reveal finer details about the spatial distribution of optical properties within the lesion that may be helpful in diagnosing the breast lesion. This strategy of data acquisition may also be used for example to find the biodistribution of a compound by CW, while TD measurements of the regions comprising the compound may serve to calculate the concentration of the compound.

[0038] The TD and CW data can be acquired either sequentially or simultaneously. Sequential acquisition may be achieved for example by using a time-gated intensified CCD camera. This type of camera provides the capability for measuring optical signals both in the CW and TD modes. The CW mode data can be acquired by simply turning the time gate off. Alternatively TD and CW data can be acquired using optic components that are exclusively designed for one mode.

[0039] Advantageously, the CW and TD data can be acquired using a gated ICCD camera. The advent of the gated intensified charged coupled device (ICCD) has permitted that significant number of time-domain spatial measurements be performed simultaneously. Moreover, when the gate is turned off the camera works in a CW mode, thus obviating the need for a separate CW and TD hardware. An image sequence of CW mode, TD mode data acquisition can thus be obtained

[0040] Simultaneous acquisition may be achieved by acquiring the TD and CW data at different wavelengths thereby permitting spectral discrimination and simultaneous acquisition. In this case the acquisition of the optical signal is performed at a plurality of wavelengths and the CW and TD data are combined to reconstruct an image.

[0041] In a preferred embodiment certain specific time points or intervals of time (time gates) of the TPSF at which TD data will be acquired are selected. The determination of the time gates is preferably based on the following approach:

[0042] A noiseless TPSF is a continuous and infinitely differentiable function defined on R+. Critical points of a function can be identified via zeros of this function's derivative. Due to the fact that a TPSF has a characteristic shape, the ith derivative will yield a set of points where the derivative became zero, which corresponds to extreme values of the underlying function. The first subset s₁={s_(1,1)} corresponding to the 1^(st) derivative describes the unique TPSF maximum. The second subset s₂={s_(2,1);s_(2,2)} corresponding to the 2^(nd) derivative reveals two points where the curvature directionality changed. Derivatives of the higher order yield information on more subtle details of the TPSF shape. The subset s_(i) can be defined as s_(i)={s_(i,1); . . . ;s_(i,i)} for the case of continuous TPSF.

[0043] Given a TPSF f(x) represented with a set of M values (M>>N), confined within an interval [a_(o),b_(o)] one can perform recursive numerical “differentiation” of the TPSF and of its' “derivatives” by computing the quotient: ${Q_{i} = \frac{{f\left( x_{i + 1} \right)} - {f\left( x_{i - 1} \right)}}{x_{i + 1} - x_{i - 1}}},{x_{i} \geq a_{0}},{x_{M} \leq b_{0}}$

[0044] which would approximate the value of f′(x₁).

[0045] When plotted, characteristic sequence of functions will emerge as shown in FIGS. 3A and 3B. In this example, one observes that: s₁={31.5}, s₂={20.5; 40.5}, s₃={14.5; 25.5; 48.5}.

[0046] In order to obtain an adequate TPSF representation with N points or time gates, one would want to reflect the TPSF shape as fully as possible. The sequence of numbers {s₁;s₂; . . . } allows for identification of the most relevant points in the order of diminishing significance as the subset number increases. Elements within a given subset s_(i) have equal significance.

[0047] One can replace s_(i) with:

s _(i)′≡{(s _(i,1)−0.5r,s _(i,1)+0.5r); . . . ;(s _(1,i)−0.5r,s _(i,i)+0.5r)}

[0048] where r is the width of a time gate. The set s_(i)′ is a collection of intervals rather than points.

[0049] In the case where several partial TPSF's are to be acquired, when for example different source-detector configurations are used, the procedure outlined above can yield S^(i)={s₁ ^(i);s₂ ^(i); . . . }; i=1, . . . , K for a given TPSF where K is chosen a priori. In order to reflect the most relevant features of the set of TPSFs, the union of the nth derivative zeros is obtained. For example S₁=s₁ ¹∪ s₁ ²∪ . . . ∪s₁ ^(k), S₂=s₂ ¹∪ s₂ ²∪ . . . ∪s₂ ^(k) and so on. The set {S₁;S₂, . . . } provides a sequence of numbers that should be used to represent the set of K TPSFs in an optimal manner.

[0050] As above, s_(i) might be replaced with s_(i)′ in order to analyze time gates instead of time points.

[0051] In one embodiment of the invention the steps to select the appropriate time points or time gates are as follows:

[0052] Acquire TPSFs with high temporal resolution for all source-detector pairs that are capable of functioning simultaneously. At least one typical source position should be used. Robustness of the subsequent analysis increases, as more typical source positions are included.

[0053] Approximate all measured TPSFs with curves based on a model of photon propagation.

[0054] Perform analysis as described above to determine the N time gates to be used during acquisition.

[0055] Acquire data with the N points of the set {S₁;S₂, . . . }.

[0056] Preferably N is an input parameter. In practice it will be determined via estimation of the resulting data set size that can be used to reconstruct images within desired time frame. One might want to estimate N as well in case data set size is not an issue.

[0057] Time window [a₀,b₀]⊂R⁺ used for initial data acquisition is assumed an input parameter. However, it should be chosen wide enough based on prior knowledge in order to maximize chances of capturing most significant TPSF features.

[0058] Temporal sampling, i.e. the distance between x_(i) and x_(i+1) is an input parameter.

[0059] Temporal resolution r₀, i.e. the minimal distance between x_(i) and x_(i+1) that yields “uncorrelated” values f(x₁) and f(x_(i+1)), comes primarily from the limitations of the data acquisition hardware and is, therefore, an input parameter.

[0060] It is preferable to perform initial data acquisition with the steps of not more than 0.5×r₀ and time gate width of not more than r₀. Eventual time gate width r≧r₀ might be chosen to minimize data set size while preserving the distinct TPSF features revealed by the analysis. For example, distinct points s_(i,j) and s_(i′,j′) would fall within the same time gate if |s_(i,j)−s_(i′,j′)|<r.

[0061] The use of variable time gate widths may yield superior results. One would replace s_(i)′ with s_(i)″≡{(s_(i,1)−0.5r_(i,1),s_(i,1)+0.5r_(i,1)); . . . ;(s_(i,i)−0.5r_(i,i),s_(i,i)+0.5r_(i,i))} to analyze this case.

[0062] The selected time gates may be used to reconstruct the TPSF. Constraints may be used in the reconstruction. For example, the integrated TPSF may be constrained to a value substantially identical to a measured attenuation value obtained by CW measurements. Further, the number of time points or time gates that is necessary to acquire in order to reconstruct an acceptable image is reduced because of the additional information conveyed by the CW measurements.

[0063] With partial TPSF acquisition, gated ICCD camera may allow acquisition of CW and TD data according to predetermined sequences as would be obvious to one skilled in the art. Zoom lenses may also be used to obtain CW data in full field mode and TD data by zooming in on a desired VOI.

[0064] The embodiment(s) of the invention described above is(are) intended to be exemplary only. The scope of the invention is therefore intended to be limited solely by the scope of the appended claims. 

I/we claim:
 1. A method for optical imaging of a volume of interest (VOI) in a turbid medium, the method comprising: i) optically scanning the VOI at a plurality of source/detector geometries using continuous wave (CW) to generate CW data; ii) optically scanning the VOI at a plurality of source/detector geometries using time-domain (TD) to generate data representing at least a portion of a measured temporal point spread function (TPSF), said TPSF data being measured from a plurality of light pulses from which a statistical average of light received as a function of time is obtained, said TPSF data yielding information about absorption and scatter within said VOI; iii) combining information extracted from the CW data with the TPSF data to improve an accuracy of imaging using the measured TPSF data, whereby an improved image accuracy of the VOI is generated with fewer said light pulses and a shorter acquisition time by using both time-domain and continuous wave modalities.
 2. The method as claimed in claim 1 wherein the step of combining comprises: i) estimating a value of one or more optical property within the VOI using the measured TPSF; ii) calculating an attenuation value using the estimated optical properties; iii) comparing the calculated attenuation value with the CW data to obtain a difference value; iv) repeating steps i) to iii) until the difference value is less than a predetermined value.
 3. The method as claimed in claim 2 wherein said step of calculating comprises using a CW photon migration model.
 4. The method as claimed in claim 1 wherein said step of combining comprises: i) estimating a value of one or more optical property using TD measurements; ii) estimating said value of one or more optical property using CW measurements; iii) comparing said value of one or more optical property obtained by TD with said one or more optical property obtained by CW; iv) adjusting said CW and TD estimations of said value of one or more optical property until said estimations converge to a predetermined range.
 5. The method as claimed in claim 4 wherein the one or more optical property is selected from absorption coefficient, scattering coefficient and a combination thereof.
 6. The method as claimed in claim 5 wherein said one or more optical properties are said absorption coefficient and said scatter coefficient and wherein prior to estimating a value of said absorption and scatter coefficients using TD measurements, said absorption coefficient is estimated using CW measurements while keeping said scatter coefficient constant.
 7. The method as claimed in claim 19 further comprising a step of normalizing said measured TPSF data relative to said CW data prior to combining the information to generate dimensionless data thereby providing quicker data processing.
 8. The method as claimed in claim 1 wherein the TPSF and CW data are measured sequentially.
 9. The method as claimed in claim 1 wherein the TPSF and CW data are measured using a gated ICCD camera, providing from each said light pulse an intensity value within at least one selected time gate.
 10. The method as claimed in claim 1 wherein the TPSF and CW data are measured at a plurality of wavelengths and wherein the TPSF and attenuation value are acquired simultaneously at different wavelengths.
 11. The method as claimed in claim 1 wherein a partial TPSF is measured.
 12. The method as claimed in claim 11 wherein the partial TPSF comprises one or more predetermined time gate.
 13. A method for optical imaging of a volume of interest (VOI) in a turbid medium, the method comprising: i) obtaining continuous wave (CW) data to generate an image of a part of the medium comprising the VOI; ii) localizing the VOI within the part of the medium; and iii) obtaining time-domain (TD) data from the localized VOI to generate an image of the localized VOI.
 14. A method for optical imaging of a volume of interest (VOI) in a turbid medium, the method comprising: i) obtaining continuous wave (CW) data to generate an image of a part of the medium comprising the VOI; ii) localizing the VOI within the part of the medium; iii) optimizing TD image acquisition parameters using the CW data; and iv) obtaining TD data from the VOI using the optimized TD image acquisition parameters to generate an image of the localized VOI.
 15. The method as claimed in claim 14 wherein said step of optimizing comprises selecting one or more source/detector geometries used to generate CW data for use in obtaining TD data of the VOI.
 16. An optical imaging system for imaging a turbid media object, the apparatus comprising: at least one optical source for providing continuous and pulsed optical energy; at least one optical detector for detecting optical energy and generating time-dependent and continuous data; a source/object optical coupling for coupling said optical source to a desired position on said object; a detector/object optical coupling for coupling said optical detector to a desired position on said object; an acquisition controller connected to said optical source and said optical detector for collecting said time-dependent and continuous data for a plurality of source/detector geometries within a volume of interest in said object; a continuous-wave photon migration model calculator; a time-domain photon migration model calculator; and an estimator using said continuous data and calculated values corresponding to said continuous data to improve a determination of optical properties of said object using said time-dependent data and calculated values corresponding to said time-dependent data.
 17. The system as claimed in claim 16 further comprising a raw TPSF data compiler for receiving a time-dependent output signal from said detector and generating raw TPSF data output.
 18. The system as claimed in claim 17 wherein said TPSF data compiler comprises a TPSF data normalizer for normalizing said TPSF data with said continuous data.
 19. The system as claimed in claim 16 wherein said source comprises one or more laser source.
 20. The system as claimed in claim 16 wherein said source/object and detector/object optical couplings for coupling said optical source and said optical detector with said object are selected from fiber optics, free-space optics and a combination thereof.
 21. The system as claimed in claim 20 wherein said source/object and said detector/object optical couplings are free-space optics and wherein said free-space optics comprise mirrors to directionally propagate light so that the light is injected and collected from desired areas on said object.
 22. The system as claimed in claim 21 wherein said mirrors are mirrors galvanometers.
 23. The system as claimed in claim 20 wherein said source/object and said detector/object optical couplings comprise a plurality of fiber optics and optical switches to select desired fiber optics for light injection and detection.
 24. The system as claimed in claim 16 wherein said source/object optical couplings comprise a plurality of light injection ports and collection ports for coupling said optical source and said optical detector respectively with said tissue.
 25. The system as claimed in claim 16 wherein said optical source provide optical energy at a plurality of wavelengths simultaneously.
 26. The system as claimed in claim 25 wherein said optical detector detects optical energy at a plurality of wavelengths simultaneously.
 27. The system as claimed in claims 16 wherein said acquisition controller is used to adjust said optical source intensity as a function of said detected optical energy for optimizing signal to noise ratio.
 28. The system as claimed in claim 16 further comprising a display for displaying a reconstituted image of said tissue.
 29. The system as claimed in claim 16 further comprising means for selecting one or more detection wavelength.
 30. The system as claimed in claim 29 wherein said means for selecting is a filter. 